Method and system for management of diabetes with a glucose monitor and infusion pump to provide feedback on bolus dosing

ABSTRACT

Described and illustrated is a system for management of diabetes that includes an infusion pump, glucose sensor and controller with a method programmed into the controller. The infusion pump is configured to deliver insulin to a subject. The system provides the user with the ability to understand the effects of bolus insulin dosing upon their glucose levels. Specifically, the system provides a message that must include: (a) the trend of the user&#39;s glucose; (b) the recommended bolus; and (c) the actual bolus.

CROSS-REFERENCE

This application is a divisional application of U.S. patent applicationSer. No. 14/098,353, filed on Dec. 5, 2013, which application isincorporated by reference herein in its entirety.

BACKGROUND

Diabetes mellitus is a chronic metabolic disorder caused by an inabilityof the pancreas to produce sufficient amounts of the hormone insulin,resulting in the decreased ability of the body to metabolize glucose.This failure leads to hyperglycemia, i.e. the presence of an excessiveamount of glucose in the blood plasma. Persistent hyperglycemia and/orhypoinsulinemia has been associated with a variety of serious symptomsand life threatening long term complications such as dehydration,ketoacidosis, diabetic coma, cardiovascular diseases, chronic renalfailure, retinal damage and nerve damages with the risk of amputation ofextremities. Because restoration of endogenous insulin production is notyet possible, a permanent therapy is necessary which provides constantglycemic control in order to always maintain the level of blood glucosewithin normal limits. Such glycemic control is achieved by regularlysupplying external insulin to the body of the patient to thereby reducethe elevated levels of blood glucose.

External biologic such as insulin was commonly administered by means ofmultiple daily injections of a mixture of rapid and intermediate actingdrugs via a hypodermic syringe. It has been found that the degree ofglycemic control achievable in this way is suboptimal because thedelivery is unlike physiological hormone production, according to whichhormone enters the bloodstream at a lower rate and over a more extendedperiod of time. Improved glycemic control may be achieved by theso-called intensive hormone therapy which is based on multiple dailyinjections, including one or two injections per day of a long actinghormone for providing basal hormone and additional injections of rapidlyacting hormone before each meal in an amount proportional to the size ofthe meal. Although traditional syringes have at least partly beenreplaced by insulin pens, the frequent injections are nevertheless veryinconvenient for the patient, particularly those who are incapable ofreliably self-administering injections.

Substantial improvements in diabetes therapy have been achieved by thedevelopment of the drug delivery device, relieving the patient of theneed for syringes or drug pens and the administration of multiple dailyinjections. The drug delivery device allows for the delivery of drug ina manner that bears greater similarity to the naturally occurringphysiological processes and can be controlled to follow standard orindividually modified protocols to give the patient better glycemiccontrol.

In addition, delivery directly into the intraperitoneal space orintravenously can be achieved by drug delivery devices. Drug deliverydevices can be constructed as an implantable device for subcutaneousarrangement or can be constructed as an external device with an infusionset for subcutaneous infusion to the patient via the transcutaneousinsertion of a catheter, cannula or a transdermal drug transport such asthrough a patch. External drug delivery devices are mounted on clothing,hidden beneath or inside clothing, or mounted on the body and aregenerally controlled via a user interface built-in to the device or on aseparate remote device.

Blood or interstitial glucose monitoring is required to achieveacceptable glycemic control. For example, delivery of suitable amountsof insulin by the drug delivery device requires that the patientfrequently determines his or her blood glucose level and manually inputthis value into a user interface for the external pumps, which thencalculates a suitable modification to the default or currently in-useinsulin delivery protocol, i.e., dosage and timing, and subsequentlycommunicates with the drug delivery device to adjust its operationaccordingly. The determination of blood glucose concentration istypically performed by means of an episodic measuring device such as ahand-held electronic meter which receives blood samples via enzyme-basedtest strips and calculates the blood glucose value based on theenzymatic reaction.

Continuous glucose monitoring (CGM) has also been utilized over the lasttwenty years with drug delivery devices to allow for closed loop controlof the insulin(s) being infused into the diabetic patients. To allow forclosed-loop control of the infused insulins,proportional-integral-derivative (“PID”) controllers have been utilizedwith mathematical model of the metabolic interactions between glucoseand insulin in a person. The PID controllers can be tuned based onsimple rules of the metabolic models. However, when the PID controllersare tuned or configured to aggressively regulate the blood glucoselevels of a subject, overshooting of the set level can occur, which isoften followed by oscillations, which is highly undesirable in thecontext of regulation of blood glucose. Alternative controllers wereinvestigated. It was determined that a model predictive controller(“MPC”) used in the petrochemical industries where processes involvedlarge time delays and system responses, was the most suitable for thecomplex interplay between insulin, glucagon, and blood glucose. The MPCcontroller has been demonstrated to be more robust than PID because MPCconsiders the near future effects of control changes and constraints indetermining the output of the MPC whereas PID typically involves onlypast outputs in determining future changes. Constraints can beimplemented in the MPC controller such that MPC prevents the system fromrunning away when the limit has already been reached. Another benefit ofMPC controllers is that the model in the MPC can, in some cases,theoretically compensate for dynamic system changes whereas a feedbackcontrol, such as PID control, such dynamic compensation would not bepossible.

MPC can be viewed therefore as a combination of feedback and feedforward control. MPC, however, typically requires a metabolic model tomimic as closely as possible the interaction between insulin and glucosein a biological system. As such, due to person-to-person biologicalvariations, MPC models continue to be further refined and developedpresently. As informational background on MPC relating to details of theMPC controllers, variations on the MPC, and mathematical modelsrepresenting the complex interaction of glucose and insulin, all ofwhich are shown and described in the following documents:

-   U.S. Pat. No. 7,060,059;-   US Patent Application Nos. 2011/0313680 and 2011/0257627,-   International Publication WO 2012/051344,-   Percival et al., “Closed-Loop Control and Advisory Mode Evaluation    of an Artificial Pancreatic β Cell: Use of    Proportional-Integral-Derivative Equivalent Model-Based Controllers”    Journal of Diabetes Science and Technology, Vol. 2, Issue 4, July    2008.-   Paola Soru et al., “MPC Based Artificial Pancreas; Strategies for    Individualization and Meal Compensation” Annual Reviews in Control    36, p. 118-128 (2012),-   Cobelli et al., “Artificial Pancreas: Past, Present, Future”    Diabetes Vol. 60, November 2011;-   Magni et al., “Run-to-Run Tuning of Model Predictive Control for    Type 1 Diabetes Subjects: In Silico Trial” Journal of Diabetes    Science and Technology, Vol. 3, Issue 5, September 2009.-   Lee et al., “A Closed-Loop Artificial Pancreas Using Model    Predictive Control and a Sliding Meal Size Estimator” Journal of    Diabetes Science and Technology, Vol. 3, Issue 5, September 2009;-   Lee et al., “A Closed-Loop Artificial Pancreas based on MPC: Human    Friendly Identification and Automatic Meal Disturbance Rejection”    Proceedings of the 17^(th) World Congress, The International    Federation of Automatic Control, Seoul Korea Jul. 6-11, 2008;-   Magni et al., “Model Predictive Control of Type 1 Diabetes: An in    Silico Trial” Journal of Diabetes Science and Technology, Vol. 1,    Issue 6, November 2007;-   Wang et al., “Automatic Bolus and Adaptive Basal Algorithm for the    Artificial Pancreatic β-Cell” Diabetes Technology and Therapeutics,    Vol. 12, No. 11, 2010; and-   Percival et al., “Closed-Loop Control of an Artificial Pancreatic    β-Cell Using Multi-Parametric Model Predictive Control” Diabetes    Research 2008.

All articles or documents cited in this application are herebyincorporated by reference into this application as if fully set forthherein.

SUMMARY OF THE DISCLOSURE

Applicants have devised a technique that allows for a method foroperating a diabetes management system to manage diabetes of a user. Thesystem has an infusion pump, at least one glucose monitor and acontroller. The method can be achieved by: determining a glucosemeasurement in which a fluid sample with glucose is transformed intoenzymatic byproducts by application of electrical signals to the sample;calculating a bolus recommendation based on the glucose measurement madeby the determining step; evaluating whether the bolus recommendation wasfollowed by a user of the system; in the event the bolus recommendationwas not followed by the user then: storing the actual bolus delivered bythe infusion pump; measuring the glucose value in subsequent fluidsamples and if the glucose values over time is greater than apredetermined high trend threshold then annunciating a high glucosetrend, along with the recommended bolus and the actual bolus deliveredby the pump otherwise if the glucose values over time is less than apredetermined low trend threshold then annunciating a low glucose trendalong with both the recommended bolus and the actual bolus delivered bythe pump.

In yet another aspect, a system for management of diabetes is providedthat includes an episodic glucose meter, continuous glucose meter, andan infusion pump coupled to a controller. The episodic glucose meter isconfigured to measure glucose level in a fluid sample of a subject atdiscrete non-uniform time intervals and provide such episodic glucoselevel as input data for bolus calculation; a continuous glucose monitorto continuously measure glucose level of the subject at discrete,generally uniform time intervals and provide the glucose level at eachinterval in the form of glucose measurement data that can be used forbolus calculation. The insulin infusion pump is configured to deliverinsulin to the subject; a microcontroller in communication with thepump, glucose meter and the glucose monitor. The controller isconfigured to provide a bolus recommendation to the subject, evaluatewhether an actual bolus delivered by the pump is other than the bolusrecommendation. In the event the actual bolus delivered is other thanthe bolus recommendation, the system determines a trend of glucosevalues over a period of time and annunciates one of a low trend or hightrend to the user along with actual bolus delivered and bolusrecommendation.

In each of the above aspects, the following features may also beutilized in combination with each of the aspects. For example, thesystem may store the glucose measurement made by the measuring step inthe controller; the system may ascertain a need for another bolusrecommendation; the system may determine a declining rate of change inthe glucose measurements of fluid samples of the user; the glucosemonitor may include a continuous glucose monitor; the annunciating ofthe high glucose trend may include displaying a message that a trend ofglucose measurements is increasing after a bolus delivery along withboth the recommended bolus and the actual bolus delivered; theannunciating of the low glucose trend may include displaying a textualmessage that a trend of glucose measurements is decreasing after a bolusdelivery along with both the recommended bolus and the actual bolusdelivered; the low trend threshold may include a decreasing or negativerate of change of 20 mg/dL per every thirty minutes and the high trendthreshold may include an increasing or positive rate of change of 20mg/dL per thirty minutes.

These and other embodiments, features and advantages will becomeapparent to those skilled in the art when taken with reference to thefollowing more detailed description of various exemplary embodiments ofthe invention in conjunction with the accompanying drawings that arefirst briefly described.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated herein and constitutepart of this specification, illustrate presently preferred embodimentsof the invention, and, together with the general description given aboveand the detailed description given below, serve to explain features ofthe invention (wherein like numerals represent like elements).

FIG. 1 illustrates the system in which a controller for the pump orglucose monitor(s) is separate from both the infusion pump and theglucose monitor(s) and in which a network can be coupled to thecontroller to provide near real-time monitoring.

FIG. 2 illustrates an exemplary embodiment of the diabetic managementsystem in schematic form.

FIG. 3 illustrates the logic utilized in the controller of FIG. 1 orFIG. 2;

FIGS. 4A and 4B illustrate messages from the system; and

FIG. 5 illustrates a graphical and textual message of the system;

MODES FOR CARRYING OUT THE INVENTION

The following detailed description should be read with reference to thedrawings, in which like elements in different drawings are identicallynumbered. The drawings, which are not necessarily to scale, depictselected embodiments and are not intended to limit the scope of theinvention. The detailed description illustrates by way of example, notby way of limitation, the principles of the invention. This descriptionwill clearly enable one skilled in the art to make and use theinvention, and describes several embodiments, adaptations, variations,alternatives and uses of the invention, including what is presentlybelieved to be the best mode of carrying out the invention.

As used herein, the terms “about” or “approximately” for any numericalvalues or ranges indicate a suitable dimensional tolerance that allowsthe part or collection of components to function for its intendedpurpose as described herein. In addition, as used herein, the terms“patient,” “host,” “user,” and “subject” refer to any human or animalsubject and are not intended to limit the systems or methods to humanuse, although use of the subject invention in a human patient representsa preferred embodiment. Furthermore, the term “user” includes not onlythe patient using a drug infusion device but also the caretakers (e.g.,parent or guardian, nursing staff or home care employee). The term“drug” may include hormone, biologically active materials,pharmaceuticals or other chemicals that cause a biological response(e.g., glycemic response) in the body of a user or patient.

FIG. 1 illustrates a drug delivery system 100 according to an exemplaryembodiment that utilizes the principles of the invention. Drug deliverysystem 100 includes a drug delivery device 102 and a remote controller104. Drug delivery device 102 is connected to an infusion set 106 viaflexible tubing 108.

Drug delivery device 102 is configured to transmit and receive data toand from remote controller 104 by, for example, radio frequencycommunication 112. Drug delivery device 102 may also function as astand-alone device with its own built in microcontroller. In oneembodiment, drug delivery device 102 is an insulin infusion device andremote controller 104 is a hand-held portable controller. In such anembodiment, data transmitted from drug delivery device 102 to remotecontroller 104 may include information such as, for example, insulindelivery data, glucose information, basal, bolus, insulin tocarbohydrates ratio or insulin sensitivity factor, to name a few. Themicrocontroller 104 is configured to include an MPC controller 10 thathas been programmed to receive continuous glucose readings from a CGMsensor 112. Data transmitted from remote microcontroller 104 to insulindelivery device 102 may include glucose test results and a food databaseto allow the drug delivery device 102 to calculate the amount of insulinto be delivered by drug delivery device 102. Alternatively, the remotemicrocontroller 104 may perform basal dosing or bolus calculation andsend the results of such calculations to the drug delivery device. In analternative embodiment, an episodic blood glucose meter 114 may be usedalone or in conjunction with the CGM sensor 112 to provide data toeither or both of the microcontroller 104 and drug delivery device 102.Alternatively, the remote microcontroller 104 may be combined with themeter 114 into either (a) an integrated monolithic device; or (b) twoseparable devices that are dockable with each other to form anintegrated device. Each of the devices 102, 104, and 114 has a suitablemicro-controller (not shown for brevity) programmed to carry out variousfunctionalities.

Drug delivery device 102 may also be configured for bi-directionalwireless communication with a remote health monitoring station 116through, for example, a wireless communication network 118. Remotecontroller 104 and remote monitoring station 116 may be configured forbi-directional wired communication through, for example, a telephoneland based communication network. Remote monitoring station 116 may beused, for example, to download upgraded software to drug delivery device102 and to process information from drug delivery device 102. Examplesof remote monitoring station 116 may include, but are not limited to, apersonal or networked computer 126, server 128 to a memory storage, apersonal digital assistant, other mobile telephone, a hospital basemonitoring station or a dedicated remote clinical monitoring station.

Drug delivery device 102 includes electronic signal processingcomponents including a central processing unit and memory elements forstoring control programs and operation data, a radio frequency module116 for sending and receiving communication signals (i.e., messages)to/from remote controller 104, a display for providing operationalinformation to the user, a plurality of navigational buttons for theuser to input information, a battery for providing power to the system,an alarm (e.g., visual, auditory or tactile) for providing feedback tothe user, a vibrator for providing feedback to the user, a drug deliverymechanism (e.g. a drug pump and drive mechanism) for forcing insulinfrom an insulin reservoir (e.g., an insulin cartridge) through a sideport connected to an infusion set 108/106 and into the body of the user.An example of a drug delivery device 102 (or pump 16) can be in the formof a modified Animas Vibe insulin pump manufactured by AnimasCorporation in Wayne, Pa. USA.

Glucose levels or concentrations can be determined by the use of the CGMsensor 112. The CGM sensor 112 utilizes amperometric electrochemicalsensor technology to measure glucose with three electrodes operablyconnected to the sensor electronics and are covered by a sensingmembrane and a biointerface membrane, which are attached by a clip.

The top ends of the electrodes are in contact with an electrolyte phase(not shown), which is a free-flowing fluid phase disposed between thesensing membrane and the electrodes. The sensing membrane may include anenzyme, e.g., glucose oxidase, which covers the electrolyte phase. Inthis exemplary sensor, the counter electrode is provided to balance thecurrent generated by the species being measured at the workingelectrode. In the case of a glucose oxidase based glucose sensor, thespecies being measured at the working electrode is H₂O₂. The currentthat is produced at the working electrode (and flows through thecircuitry to the counter electrode) is proportional to the diffusionalflux of H₂O₂ generated by this electrochemical transformation of glucoseinto its enzymatic byproducts. Accordingly, a raw signal may be producedthat is representative of the concentration of glucose in the user'sbody, and therefore may be utilized to estimate a meaningful glucosevalue. Details of the sensor and associated components are shown anddescribed in U.S. Pat. No. 7,276,029, which is incorporated by referenceherein as if fully set forth herein this application. In one embodiment,a continuous glucose sensor from the Dexcom Seven System® (manufacturedby Dexcom Inc.) can also be utilized with the exemplary embodimentsdescribed herein.

In one embodiment of the invention, the following components can also beutilized as a system for management of diabetes that is akin to anartificial pancreas: OneTouch Ping® Glucose Management System by AnimasCorporation that includes at least an infusion pump and an episodicglucose sensor; and DexCom® G4 Platinum® CGM by DexCom Corporation withinterface to connect these components and programmed in MATLAB® languageand accessory hardware to connect the components together; and controlalgorithms in the form of an MPC that automatically regulates the rateof insulin delivery based on the glucose level of the patient,historical glucose measurement and anticipated future glucose trends,and patient specific information.

FIG. 2 illustrates a schematic diagram 200 of the system 100 in FIG. 1programmed with the solution devised by applicants to counteract a lessthan desirable effect of a closed-loop control system. In particular,FIG. 2 provides for an MPC programmed into a control logic module 10that is utilized in controller 104. MPC logic module 10 receives adesired glucose concentration or range of glucose concentration 12(along with any modification from an update filter 28 so that it is ableto maintain the output (i.e., glucose level) of the subject within thedesired range of glucose levels.

Referring to FIG. 2, the first output 14 of the MPC-enabled controllogic 10 can be a control signal to an insulin pump 16 to deliver adesired quantity of insulin 18 into a subject 20 at predetermined timeintervals, which can be indexed every 5 minutes using time intervalindex k. A second output in the form of a predicted glucose value 15 canbe utilized in control junction B. A glucose sensor 22 (or 112 inFIG. 1) measures the glucose levels in the subject 20 in order toprovide signals 24 representative of the actual or measured glucoselevels to control junction B, which takes the difference betweenmeasured glucose concentration 24 and the MPC predictions of thatmeasured glucose concentration. This difference provides input for theupdate filter 26 of state variables of the model. The difference 26 isprovided to an estimator (also known as an update filter 28) thatprovides for estimate of state variables of the model that cannot bemeasured directly. The update filter 28 is preferably a recursive filterin the form of a Kalman filter with tuning parameters for the model. Theoutput of the update or recursive filter 28 is provided to controljunction A whose output is utilized by the MPC in the control logic 10to further refine the control signal 14 to the pump 16 (or 102 in FIG.1). A tuning factor 34 is used with the MPC controller 10 to “tune” thecontroller in its delivery of the insulin. To accomplish this,applicants have devised the use of a calibration index module 30 anddata omission module 32 to adjust the tuning factor. Calibration indexmodule 30 is configured to track the number of glucose measurementcalibration, which is typically accomplished by an episodic glucosemonitor, such as, for example, a blood glucose test strip and metersystem. Data omission index module 32 is configured to track the numberof missing measurements or data from the continuous glucose monitor 22.

Details of the closed-loop controller are provided in U.S. patentapplication Ser. No. 13/834,571 filed on Mar. 15, 2013 which is herebyincorporated by reference as if fully set forth herein.

FIG. 3 illustrates logical process 300 that can be utilized (withappropriate modifications that are well within the capabilities of oneskilled in the field) for either system 100 or system 200. Process 300starts with a decision (by the user or the controller) at step 302 toconduct a glucose measurement in a fluid sample (e.g., blood orinterstitial fluid). The glucose in the fluid sample is then physicallytransformed into enzymatic byproducts due to the electrochemicalreaction with the enzyme on the glucose sensing electrodes. At step 304,a bolus amount of insulin is calculated. The insulin bolus calculationis known in the art, such as, for example, shown and described in USPatent Application Publication 20120095318 or U.S. Pat. Nos. 6,872,200,7,815,602, 7,819,843. At step 306, the calculated bolus is annunciatedas a recommended bolus to the user. At step 308, the system checks tosee if the user confirmed delivery of the recommended bolus amount. Ifnot, the system checks the pump at step 310 to determine the amountactually infused to the user. At step 312, if the insulin amountactually infused is less than the recommended amount, the system storesthis amount. At step 314, if the actual amount of insulin infused isgreater than the recommended, this again is stored. At step 316, thesystem monitors the continuous glucose readings for a period of time Tafter the bolus delivery. After time T, the system checks at step 318 tosee the rate of change of glucose readings is trending higher or lower.If the rate of change is trending lower then the system annunciate amessage at step 320 to the user that: (a) the glucose readings aretrending low with respect to a predetermined low trend threshold of, forexample, such as a negative decrease of about 20 mg/dL for every thirtyminutes; (b) actual amount of bolus delivered and (c) recommended bolus.On the other hand, if the rate of change of the glucose values areincreasing then the system annunciate a message at step 322 that: (a)the glucose is trending higher with respect to a predetermined hightrend threshold, such as, for example, a positive increase of about 20mg/dL for every thirty minutes, (b) actual bolus amount delivered; and(c) recommended amount. It should be understood that the blood glucoseconcentration of 20 mg/dL and the time interval of thirty minutes areonly examples and other blood glucose concentrations and time durationsare within the scope of the claimed invention. The messages provided atrespective steps 320 and 322 can be in the form shown in FIGS. 4A and 4Bon the controller or on the pump. Alternatively, the messages can begraphical and textual as shown in FIG. 5. At step 324, the system storesthe rate of change (or a flag for high trend or low trend) along withthe time stamp. At step 326, the system determines (via monitoring ofthe CGM or by user input) that there is a life event (e.g., meals,snacks, exercise, drinks, and the like) that may necessitate anotherbolus calculation. If such is the case, the system returns to the mainroutine at step 328 otherwise, the system continues monitoring theglucose levels at step 316.

Benefits of the invention are many: for example, the user is able toobtain a clear indication of the effects of insulin dosing on the user'sglucose level; the system provides nearly instantaneous feedback to theuser of the user's glucose level after a bolus dosing so that the userwould be able to determine if their recommended bolus should be followedor a dosing that is different from the recommended bolus is better forthe user.

While the invention has been described in terms of particular variationsand illustrative figures, those of ordinary skill in the art willrecognize that the invention is not limited to the variations or figuresdescribed. For example, the closed-loop controller need not be an MPCcontroller but can be, with appropriate modifications by those skilledin the art, a PID controller, a PID controller with internal modelcontrol (IMC), a model-algorithmic-control (MAC) that are discussed byPercival et al., in “Closed-Loop Control and Advisory Mode Evaluation ofan Artificial Pancreatic β Cell: Use of Proportional-Integral-DerivativeEquivalent Model-Based Controllers” Journal of Diabetes Science andTechnology, Vol. 2, Issue 4, July 2008. In addition, where methods andsteps described above indicate certain events occurring in certainorder, those of ordinary skill in the art will recognize that theordering of certain steps may be modified and that such modificationsare in accordance with the variations of the invention. Additionally,certain of the steps may be performed concurrently in a parallel processwhen possible, as well as performed sequentially as described above.Therefore, to the extent there are variations of the invention, whichare within the spirit of the disclosure or equivalent to the inventionsfound in the claims, it is the intent that this patent will cover thosevariations as well.

What is claimed is:
 1. A method for operating a diabetes managementsystem having an infusion pump, at least one glucose monitor and amicrocontroller, the method comprising the following steps performedwith the microcontroller: determining a glucose measurement in which afluid sample with glucose is transformed into enzymatic byproducts byapplication of electrical signals to the sample; calculating a bolusrecommendation based on the glucose measurement made by the determiningstep; evaluating whether the bolus recommendation was followed by a userof the system; in the event the bolus recommendation was not followed bythe user then: storing the actual bolus delivered by the infusion pump;measuring the glucose value in subsequent fluid samples and if theglucose values over time is greater than a predetermined high trendthreshold then annunciating a high glucose trend, along with therecommended bolus and the actual bolus delivered by the pump otherwiseif the glucose values over time is less than a predetermined low trendthreshold then annunciating a low glucose trend along with both therecommended bolus and the actual bolus delivered by the pump.
 2. Themethod of claim 1, further comprising the step of storing the glucosemeasurement made by the measuring step in the controller.
 3. The methodof claim 1, further comprising the step of ascertaining a need foranother bolus recommendation due to an input to the controller.
 4. Themethod of claim 1, in which the ascertaining comprises a declining rateof change in the glucose measurements of fluid samples of the user. 5.The method of claim 1, in which the glucose monitor comprises acontinuous glucose monitor and the microcontroller comprises aclosed-loop controller.
 6. The method of claim 5, in which theannunciating of the high glucose trend comprises displaying a messagethat a trend of glucose measurements is increasing after a bolusdelivery along with both the recommended bolus and the actual bolusdelivered.
 7. The method of claim 5, in which the annunciating of thelow glucose trend comprises displaying a textual message that a trend ofglucose measurements is decreasing after a bolus delivery along withboth the recommended bolus and the actual bolus delivered.
 8. The methodof claim 1, in which the low trend threshold comprises a decreasing rateof glucose concentration about 20 mg/dL every thirty minutes and thehigh trend threshold comprises an increasing rate of change of glucoseconcentration of about 20 mg/dL every thirty minutes.